Optical coherence photoacoustic microscopy

ABSTRACT

A system and method for providing an optical coherence photoacoustic (OC-PAM) microscopy. An OC-PAM microscope includes a light source that outputs light, a scanner, a detector, a transducer, and an image processing module. The scanner receives the light and scans the light across a sample. The detector receives reflected light from the sample in response to the scanned light. The transducer detects photoacoustic waves induced in the sample by the scanned light. The image processing module receives output from the detector and the transducer and generates a photoacoustic microscopy (PAM) image and an optical coherence tomography (OCT) image based on the received output from the detector and the transducer. The PAM and OCT image data may be fused to form a single, OC-PAM image. Additionally, a series of PAM images and OCT images, respectively, may be combined to generate three-dimensional PAM and OCT images, respectively.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application claims the benefit as a continuation of and priority to U.S. patent application Ser. No. 13/524,813, filed on Jun. 15, 2012, for “OPTICAL COHERENCE PHOTOACOUSTIC MICROSCOPY”, which claims priority of U.S. Provisional application No. 61/497,323, filed on Jun. 15, 2011, for “OPTICAL COHERENCE PHOTOACOUSTIC MICROSCOPY” each of which are incorporated herein by reference in their entireties.

BACKGROUND

The present invention relates to optical coherence tomography (OCT) and photoacoustic microscopy (PAM).

SUMMARY

OCT and PAM are two microscopic three-dimensional non-invasive imaging modalities that are based on different contrast mechanisms. OCT is a low-coherent interferometer-based optical imaging modality that provides imaging of mainly the scattering properties of biological tissues. By using a broadband light source, OCT resolves the depth of a scatterer through coherence gating.

In contrast, PAM is an optical-absorption based imaging modality that detects laser-induced ultrasonic waves as a result of specific optical absorption. When short laser pulses irradiate biological tissues, optical energy is absorbed by substances like hemoglobin and melanin and converted to heat. Thermo-elastic expansions then occur, which lead to the generation of wideband ultrasonic waves. The ultrasonic waves are detected by an ultrasonic transducer and used to quantify the optical absorption properties of the sample. The waves may be used to form an image of the sample based upon the optical absorption contrast of elements of the sample, such as tissue of a biological sample.

Due to the different contrast mechanisms, OCT and PAM can provide different, but complementary, information of biological tissues. OCT images the microanatomy of a sample, such as a histology-like cross-sectional image of a retina. OCT can also measure blood flow velocity by measuring the Doppler effect impinged on the probing light. In contrast, PAM images a microvasculature and blood oxygenation by using multiple wavelength illumination.

Previously, light sources used in OCT and PAM were different. OCT generally uses near infrared, broadband and continuous light, such as produced by a superluminescent diode (SLD), or infrared, virtually continuous light, such as produced by a Ti:Sapphire laser with approximately 80 MHz pulse repetition rate. In contrast, PAM generally uses narrow band and pulsed lasers in the visible light spectrum targeting, for instance, the absorption of hemoglobin. Use of near infrared (NIR) light in OCT allows for deeper penetration depth than otherwise achievable using light in the visible spectrum. The selection of light wavelength in PAM, including whether visible light or NIR light, depends on the absorption spectrum of the targeted molecules. Additional information related to OCT and PAM imaging may be found in U.S. Pat. No. 8,025,406, the entire contents of which are hereby incorporated by reference.

Embodiments of the invention relate to systems and methods for optical coherence photoacoustic microscopy (OC-PAM), a multi-modal microscopic imaging modality that can simultaneously image the absorption and scattering contrasts of biological tissues non-invasively. OC-PAM uses one light source, such as a pulsed broadband laser or a swept laser that outputs pulsed swept laser light of a plurality of wavelengths in a short scan period (e.g., less than 10 nanoseconds (ns)), to simultaneously achieve both PAM functions, by detecting the absorption-induced photoacoustic waves, and OCT functions, by detecting the reflected light using an interferometer. In OC-PAM imaging, with each laser pulse, an A-scan is generated for both OCT and PAM, respectively. Additionally, OC-PAM imaging generates inherently registered PAM and OCT images, providing an ability to study the scattering and absorption of biological tissues.

Embodiments of the invention can be used for OC-PAM imaging of a biological sample, such as a human eye. For example, light of the OC-PAM microscopes disclosed herein may enter through a pupil and be directed to a retinal region of interest within an eye. Additionally, the systems and methods disclosed herein may be used to image various biological samples such as cells and molecules in suspension, physiological appendages, small animal organs (e.g., ears, skin, eyes, brain, internal organs, etc.) and human eyes and skin.

In another embodiment, the invention provides an optical coherence photoacoustic microscope including a light source that outputs light, a sample, a detector, a transducer, and an image processing module. The sample receives the light, which is scanned across the sample. The detector receives reflected fight from the sample in response to the scanned light. The transducer is positioned to detect photoacoustic waves induced in the sample by the scanned light. The image processing module receives output from the transducer and the detector and generates a photoacoustic microscopy (PAM) image and an optical coherence tomography (OCT) image based on the received output from the detector and the transducer.

In another embodiment, the invention provides a method for optical coherence photoacoustic microscope. The method includes emitting light from a light source and scanning the light across a sample. A detector receives reflected light from the sample in response to the scanned light. The method further includes detecting, by a transducer, photoacoustic waves induced in the sample by the scanned light, and receiving, by an image processing module, output from the detector and the transducer. The image processing module generates a photoacoustic microscopy (PAM) image and an optical coherence tomography (OCT) image based on the received output from the detector and the transducer.

Other aspects of the invention will become apparent by consideration of the detailed description and accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates an optical coherence photoacoustic microscopy (OC-PAM) microscope in a transmission mode according to embodiments of the invention.

FIGS. 2A-D illustrate light passing through the beam splitter 150 at various stages of OC-PAM.

FIGS. 3A-B illustrate examples of optical coherence tomography (OCT) image data.

FIG. 4 A illustrates an OCT B-scan of a mouse ear generated with the OC-PAM microscope of FIG. 1.

FIG. 4B illustrates a photoacoustic microscopy (PAM) B-scan simultaneously generated with the OC-PAM microscope of FIG. 1.

FIG. 4C illustrates a fused PAM B-scan and OCT B-scan generated with the OC-PAM microscope of FIG. 1.

FIG. 5 illustrates a maximum amplitude projection (MAP) image formed from PAM B-scans generated with the OC-PAM microscope of FIG. 1.

FIG. 6 illustrates an OC-PAM method for generating OCT and PAM image data using a single light source.

FIG. 7 illustrates an OC-PAM microscope in a reaction mode according to embodiments of the invention.

DETAILED DESCRIPTION

Before any embodiments of the invention are explained in detail, it is to be understood that the invention is not limited in its application to the details of construction and the arrangement of components set forth in the following description or illustrated in the following drawings. The invention is capable of other embodiments and of being practiced or of being carried out in various ways. Also, it is to be understood that the phraseology and terminology used herein is for the purpose of description and should not be regarded as limited. The use of “including,” “comprising,” or “having” and variations thereof herein is meant to encompass the items listed thereafter and equivalents thereof as well as additional items. The terms “mounted,”“connected,” and “coupled” are used broadly and encompass both direct and indirect mounting, connecting and coupling. Further, “connected” and “coupled” are not restricted to physical or mechanical connections or couplings, and can include electrical connections or couplings, whether direct or indirect. Also, electronic communications and notifications may be performed using any known means including direct connections, wireless connections, etc.

It should be noted that a plurality of hardware and software based devices, as well as a plurality of different structural components may be utilized to implement the invention. Furthermore, and as described in subsequent paragraphs, the specific configurations illustrated in the drawings are intended to exemplify embodiments of the invention and that other alternative configurations are possible.

FIG. 1 illustrates an optical coherence photoacoustic microscopy (OC-PAM) microscope 100 according to embodiments of the invention. The microscope 100 includes a controller 105 for providing a user interface for operating and viewing images generated by the microscope 100. The controller 105 may be implemented by hardware, software, or a combination thereof. For instance, the controller 105 may include one or more of a general purpose processing unit, a digital signal processor, a field programmable gate array (FPGA), an application specific integrated circuit (ASIC), and other processing devices operable to carry out the functions attributable to the controller 105 described herein. The controller 105 may further include a memory, or be coupled to a memory, that stores instructions executed by the controller 105 to carry out the aforementioned functions, may store data for the controller 105, such as image data, and may load data to the controller 105, such as program data, calibration data, etc. for use by the controller 105 during operation of the microscope 100. Additionally, the controller 105 may include user interface components, such as a display, a graphical user interface (GUI), keyboard, mouse, touch screen, etc., to allow a user to control and interact with the microscope 100, and to view resulting images.

The controller 105 is coupled to and provides signals to a digital delay generator 110. In response to the signals from the controller 105 and a clock output, such as a clock of an analog output, the digital delay generator 110 triggers a laser 115 to output pulses. The digital delay generator 110 is also coupled to a charge coupled device (CCD) camera 120 to trigger image capture by the CCD camera 120 with appropriate timing. In some embodiments, a complementary metal-oxide-semiconductor CMOS camera is used in place of the CCD camera 120.

The laser 115 includes a broadband dye laser 125 pumped by a pump laser 130. The pump laser 130 is a frequency-double Q-switched Nd:YAG (neodymium-doped yttrium aluminum garnet) laser. For instance, the pump laser 130 may be a PSOT-10-100-532 laser sold by Elforlight Ltd., which produces a 532 nm, 10 μJ/pulse pulse with a 2 ns pulse duration, 30 kHz pulse repetition rate. The output light of the laser 115 has a center wavelength of 580 nm and a bandwidth of 20 nm with, for instance, a 5 kHz pulse repetition rate. The particular laser output may be varied depending on the application. Generally, as the center wavelength of the laser output increases, the bandwidth also increases. For example, when the laser output has a center wavelength of 830 nm, the bandwidth may be 50 nm (i.e., 830 nm+/−25 nm); and when the laser output has a center wavelength of 1000 nm, the bandwidth may be 100 nm (i.e., 830 nm+/−50 nm). In general, the square of the center wavelength divided by the bandwidth (i.e.,

$\frac{830^{2}}{50} = {\frac{688900}{50} = {13\text{,}778.}}$

is within an approximate range of about 10,000 to 20,000, although, in certain embodiments, the ratio may be higher than 20,000 or lower than 10,000. For example,

$\left( {{i.e.},\frac{{CenterWavelength}^{2}}{Bandwidth}} \right)$

In some instances, the spectrum of the laser pulses from the laser 115 has a relatively high noise level, which may reduce the quality of the OCT images acquired by the microscope 100. However, this reduction in quality may be somewhat offset by using pulsed light with stable spectral performance.

In some embodiments, the laser 115 generates output using components different than the pump laser 130 and dye laser 125. Furthermore, in some embodiments, the laser 115 is a swept laser source that outputs pulsed swept laser light of a plurality of wavelengths, which are swept in a scan period shorter than 10 ns. Alternatively, the laser 115 may be a pulsed supercontinuum light source, a pulsed broadband superluminescent diode (SLD), or a broadband Ti:Sapphire laser. Additionally, in some embodiments, the light spectrum emitted by the laser 115 may tend closer to or include near infrared (NIR) wavelengths to achieve better imaging depth and ophthalmic applications. The particular wavelengths emitted by the laser 115 may vary depending on the targeted absorber in a sample to be imaged.

The light output by the laser 115 is focused by a lens 135 on a single mode optical fiber (SMF) 140. The SMF 140 outputs the light towards a lens 145, which collimates the light and directs it to a beam-splitter cube 150 via a mirror 155 a. The light received by the beam-splitter cube 150 is split into sample arm light 160 and reference arm light 165, which is more clearly illustrated in FIGS. 2A-B. The sample arm light 160 is directed by an x-y scanner 170, under control of the controller 105, towards a lens 135 c. The lens 135 c focuses the sample arm light 160 onto a sample 180.

In response to the sample arm light 160, the sample 180 (a) reflects a portion of the light and (b) absorbs a portion of the light. The absorbed portion of light is converted to heat and causes thermo-elastic expansions to occur in the sample 180. The thermo-elastic expansions generate wideband ultrasonic waves, which are detected by an ultrasonic transducer 185. The ultrasonic transducer 185 is a needle ultrasonic transducer (30 MHz; bandwidth: 50%; active element diameter: 0.4 mm), which is inserted into a plastic tube 190 filled with ultrasonic gel. The tube 190 and transducer 185 are placed under and in physical contact with the sample 180. The transducer 185 outputs an analog signal to an amplifier 192, which outputs the signal, amplified, to a digitizer 193. The digitizer 193 is coupled to the controller 105 to provide the controller 105 with the digitized, amplified signal from the transducer 185. The distance between the ultrasonic transducer 185 and sample 180 in the application illustrated in FIG. 1 is approximately 6 mm. In other embodiments, alternate transducers configurations are used in place of the transducer 185 and/or tube 190, and may be positioned in alternate locations with respect to the sample 180, such as above the sample 180. In some embodiments, one or more of the ultrasonic transducer 185, amplifier 192, and digitizer 193 are combined into an integrated unit. In some embodiments, the transducer 185 is integrated into a contact lens for placement directly on the eye to be scanned.

After the beam splitter 150 splits the light into the sample arm 160 and the reference arm light 165, the reference arm light 165 passes through an iris 195 and is reflected by a mirror 155 b towards a mirror 155 c. The reference arm light 165 reaches a glass plate 200, which allows the majority of the reference arm light 165 to pass through to the mirror 155 c, but reflects a portion of the reference arm light 165 towards a photo diode 205. The photo diode 205 outputs a signal to the controller 105 indicating the receipt of the reflected reference arm light 165. The signal from the photo diode 205 triggers capture by the controller 105 of the digitized, amplified transducer data emitted by the digitizer 193.

The glass plate 200 is a BK7 glass plate, which is used to compensate for the group-velocity dispersion mismatch between the sample arm 160 and the reference arm 165. In some embodiments, a different glass plate is used in the microscope 100.

The reference arm light 165 that passes through the glass plate 200 is reflected by the mirror 155 c back towards the glass plate 200 and mirror 155 b. The majority of the reflected light is passed through the glass plate 200 and proceeds to the mirror 155 b, which reflects the reference arm light 165 through the iris 195 on route to the beam splitter 150. Simultaneously, the light reflected by the sample 180 passes back through the leas 135 c and is reflected by the x-y scanner 170 towards the beam splitter 150. The returning sample arm light 160 then passes through the beam splitter 150 while the returning reference arm light 165 is reflected by the beam splitter 150, resulting in the returning sample aim light 160 and reference arm light 165 being combined by the beam splitter 150. FIGS. 2C-D illustrate the combination of the sample arm light 160 and reference arm light 160 by the beam splitter 150. In some embodiments, in place of the beam splitter 150, one or more fiber couplers may be used to split and combine the sample arm light 160 and reference arm light 165. The combined light is then focused by a lens 135 d on a single mode fiber 215. The single mode Fiber 215 is a fiber optic medium that transmits the light to a detector 220 that includes a spectrometer 225 and the CCD camera 120. The combined sample arm light 160 and reference arm light 165 provide an interference pattern, as each arm has traveled approximately the same optical distance.

The spectrometer 225 includes a diffractive grating, such as a transmission grating with 1800 line pairs per millimeter (lp/mm) and an imaging lens (e.g., having f=150 mm). The diffractive grating disperses the light from the single mode fiber 215 as a line spectrum on the imaging leas, which focuses the line spectrum on the CCD camera 120. The CCD camera 120 is a line scan type, such as an Avitva-SM2-CL-2010, with 2048 pixels operating in 12-bit mode, e2V. As previously noted, the digital delay generator 110 provides a triggering signal to trigger image capture by the CCD camera 120 when the dispensed light reaches the CCD camera 120. The exposure time of the camera is based on the pulse width of the light emitted by the laser 115 and is, generally, approximately the same time length as the period of the pulse width of the light. The shutter may be open for more or less time than the period of the pulse width of the laser 115. The effective exposure time is the time that the laser is emitting light and the shutter of the camera 120 is open.

The microscope 100 scans an area (x by y) of the sample 180, one (x,y) coordinate point at a time. The image data captured by the CCD camera 120 form the OCT images, while the transducer data obtained by the transducer 185 form the PAM information.

With respect to OCT imaging, for each scanned point on the sample 180, the CCD camera 120 captures one line of image data on the CCD camera 120 for each coordinate point (an “A-scan”). FIGS. 3A-B illustrate low-pass filtered image data obtained by the CCD camera 120 based on the illumination of a single point on the sample 180. FIG. 3A illustrates the normalized intensity for the light received by the CCD camera 120 at the various wavelengths of the light as dispersed by the spectrometer 225. FIG. 3B illustrates a calculated point-spread-function (PSF) of the OCT data. In the example illustrated in FIGS. 3A-B the sample 180 was a mirror, the path length difference was set to 0.5 mm, and the exposure time of the CCD camera 120 was set to 10 μs. As shown in FIG. 3B, the measured depth resolution is 9.5 μm in air.

A cross-sectional tomograph (B-scan) may be achieved by laterally combining a series of the A-scans. Thus, after scanning the x by y area of the sample 180, three-dimensions of image data have been captured corresponding to the x-dimension of the sample 180, the y-dimension of the sample 180, and the z-dimension (depth) of the sample 180. The z-dimension is based on the spectral information, including the intensity of the various wavelengths of light received by the CCD camera 120.

FIG. 4A illustrates a B-scan OCT image 250 generated by the OCT imaging components of the microscope 100. The OCT image 250 shows a cross-section of a portion of the mouse ear. In the OCT image 250, the depth resolution is sufficient to resolve different anatomical features including the epidermis 255, dermis 260, and cartilaginous backbone 265 of the sample 180, which is a mouse ear. In this example, the OCT image reaches about half of the thickness of the mouse ear.

With respect to PAM imaging, for each scanned point on the sample 180, the transducer 185 captures ultrasound data over time to generate an A-scan image which indicates the depth of various components of the sample 180. The series of A-scan images are laterally combined to form a B-scan image having three-dimensions of ultrasound data corresponding to the x-dimension of the sample 180, the y-dimension of the sample 180, and the z-dimension (depth) of the sample 180. The z-dimension data is based on the timing of the ultrasonic waves received by the transducer.

FIG. 4B illustrates a B-scan PAM image 270 generated by the PAM imaging components of the microscope 100. The PAM image 270 shows a cross section of a portion of a mouse ear, with the cross section of blood vessels 275 of the mouse ear appearing as clusters of high amplitude ultrasonic signals. However, information about the anatomy of the tissue is not present where no significant absorption of the sample arm light 160 occured.

For example, to generate the B-scan image data for either of the B-scan OCT image 250 or the B-scan PAM image 270, while the sample arm light 160 is scanned in the one dimension (e.g., x=0 to n), the other dimension is fixed (e.g., y=0). For each x-position, an A-scan is generating, resulting in a vertical line of image data. To form the B-scan image 250 or 270, the series of vertical lines of image data are combined. Since both the OCT image 250 and PAM image 270 are generated from the same photons, they are inherently and precisely co-registered in the lateral directions (e.g., the x- and y-dimensions), which are determined by the optical scanning. In the depth direction, however, registration of the two imaging modes is not automatic. One technique for image registration in the depth direction is to first establish a relationship of the two images in the depth direction by, for instance, imaging a flat absorbing surface such as black tape. The PAM image will then be scaled and interpolated accordingly and then fused with the OCT image.

FIG. 4C illustrates an example of a fused OCT and PAM image 280, which includes a combination of the OCT image 250 and PAM image 270. The fused image 280 is a cross sectional view of the scanned portion of the mouse ear showing the blood vessels 275 of the PAM image 270 and the epidermis 255, dermis 260, and cartilaginous backbone 265 of the OCT image 250.

FIG. 5 illustrates a maximum-amplitude-projection (MAP) 285 of a 3D PAM dataset generated by the microscope 100. A series of B-scans generated by the PAM components of the microscope 100 are stacked to generate the MAP 285. The MAP 285 shows a top-down view of the sample 180, i.e., as if viewing the sample 180 from a position of the lens 135 c above the sample 180. As shown in FIG. 5, the B-scan 270 of FIG. 4B is a portion of the MAP 285 centered at the horizontal line 290. The B-scan 270, along with a series of additional B-scans, are stacked such that the blood vessels 275 of multiple B-scans combine to form the blood vessel 290 shown in FIG. 5. The PAM dataset making up the MAP 285 includes 256×256 PAM A-scans covering an area of 2.6×2.6 mm².

FIG. 6 illustrates a method 300 of generating OC-PAM images with a single light source using, for instance, the microscope 100. Accordingly, the method 300 is described with reference to the microscope 100; however, other microscopes using a single light, source may also perform the steps of method 300. In step 302, the laser 115 emits broadband pulsed light towards the beam splitter 150. In step 304, the beam splitter 150 splits the emitted broadband pulsed light into the sample arm light 160 and the reference arm light 165. In step 306, the x-y scanner 170 directs the sample arm light 160 to a point on the sample 180. A portion of the sample arm light 160 is absorbed by the sample 180 and converted into photoacoustic waves, and another portion of the sample arm light 160 is reflected by the sample 180 back toward the beam splitter 150.

In step 308 a, the photoacoustic waves generated by the sample 180 are received by the transducer 185. Meanwhile, a portion of the reference arm light 165 is reflected off of the glass 200 and is received by the photodiode 205 in step 310 a, which, in step 312 a, triggers the controller 105 to capture the PAM data received by the transducer 185. Essentially simultaneously with step 308 a, in step 308 b, the beam splitter 150 combines the portion of the sample arm light 160 reflected by the sample 180 with the reference arm light 165 returning from mirrors 155 b and 155 c, and provides the combined light to the detector 220. In step 310 b, the detector 220 is triggered by the digital delay generator 110 and, in response, in step 312 b, the detector 220 captures OCT image data generated by the combined light reaching the detector 220. The detector 220 then provides the OCT image data to the controller 105. In step 314, the OCT image data and PAM image data captured in step 312 are received by an imaging module (not shown) of the controller 105 for processing and may be saved in a memory of the controller 105.

In step 316, the controller 105 determines whether additional portions of the sample 180 remain to be scanned. If additional portions remain, the controller 300 returns to step 302 and proceeds to generate additional OCT and PAM data for the next point on the sample. Once all of the sample points of the sample 180 have been scanned as determined in step 316, the controller 105 proceeds to step 338 for image processing of the OCT and PAM data. For instance, images such as shown in FIG. 3A to 5 are generated by the imaging module of the controller 105 and saved in a memory of the controller 105 or output by the controller 105 to a display tor viewing, to another computing device for further processing or display, to a remote device over a network, to a remote storage device on a network, or to another device.

FIG. 7 illustrates an OC-PAM microscope 400 having an alternate arrangement. The microscope 400 has several components similar to the microscope 100 and such components are like-numbered. Light emitted from the laser 115 is filtered by spatial filter 405 and collimated before reaching the beam splitter 150, which, like the microscope 100, splits the emitted light into the sample arm light 160 and reference arm light 165. The microscope 400 functions with respect to the reference arm light 165 in a manner similar to the microscope 100. The sample arm light 160 is focused by the lens 135 c and scanned across the sample 180 via the x-y scanning mirror 170. In the microscope 400, the transducer 185 is positioned above the sample 180, rather than below the sample as in the microscope 100. Additionally, as an alternate to the tube 190 and ultrasound gel of the microscope 100, the transducer 185 of the microscope 400 is positioned in a water tank 410. Like the microscope 100, the microscope 400 captures OCT data with the detector 220 and PAM data with the transducer 185, which are generated based on the same photons output by the laser 115 and are, therefore, inherently and precisely co-registered in the lateral directions.

The microscopes 100 and 400 of FIGS. 1 and 7, respectively, include an x-y scanner 170 to scan the light across the sample 180. In some embodiments, however, the light from the laser 115 remains fixed while the sample 180, which is on a controlled scanning platform, is moved by the platform to scan the light across the sample 180. For instance, in these embodiments, the x-y scanner 170 may be replaced by a fixed mirror or may be held in a fixed position during a scan.

Thus, the invention provides, among other things, an OC-PAM system and method for simultaneously capturing OCT and PAM image data of a sample induced by a single light source.

In one embodiment, the invention provides an optical coherence photoacoustic microscope. The microscope includes a light source that outputs broadband pulsed light, a scanner, a Michelson interferometer with a spectrometer as a light detector, an ultrasonic transducer, and an image processing module. The scanner receives the light and scans the light across a sample. The spectrometer in a detection arm of the interferometer receives back-scattered light from the sample in response to the scanned light, which interferes with reflected light from a reference arm of the interferometer. The transducer detects photoacoustic waves induced in the sample by the scanned light in a transmission mode, where the transducer is placed on a side of the sample opposite the scanning light. The image processing module receives output from the spectrometer and the ultrasonic transducer and generates an optical coherence tomography (OCT) image and a photoacoustic microscopy (PAM) image based on the received output from the spectrometer and the transducer.

In another embodiment, the invention provides a method for optical coherence photoacoustic microscopy. In the method, broadband pulsed light is emitted from a light source and coupled into a source aim of a Michelson interferometer. The light is scanned across a sample. A spectrometer in a detection arm of the interferometer receives a combination of light back-scattered from the sample in response to the scanned light and light reflected from a reference arm of the interferometer. An ultrasonic transducer detects photoacoustic waves induced in the sample by the scanned light in a reflection mode, where the transducer is placed on a same side of the sample as the scanning light. An image processing module receives output from the spectrometer and the transducer and generates a photoacoustic microscopy (PAM) image and an optical coherence tomography (OCT) image based on the received output from the transducer and the spectrometer.

The systems and methods described herein may be used for the diagnosis and evaluation of age-related macular degeneration, geography atrophy, diabetic retinopathy, premature retinopathy, glaucoma, ocular tumors, retinal edema, retinal detachment, several types of ischemic retinopathy, and brain disorders. The systems and methods may further be used to monitor therapy on retinal diseases that use nano-particles and to provide therapy whereby the photons from the laser 115 are absorbed by the nano-particles to trigger a therapeutic reaction. Additionally, OC-PAM imaging may be used to diagnose diseases that may be diagnosed through morphology and functions of the retinal vessels, such as a stroke and Alzheimer's disease. Various features and advantages of the invention are set forth in the following claims. 

What is claimed is:
 1. A method of optical coherence photoacoustic multi-modal microscopic imaging of a target, the method comprising: generating, substantially simultaneously using a light source, A-scans for optical coherence tomography and photoacoustic microscopy of the target; forming, using a processor, B-scan images for optical coherence tomography and photoacoustic microscopy of the target using the generated A-scans; and generating, using the processor, a fused image of the target from B-scan image data for optical coherence tomography and photoacoustic microscopy, wherein the photoacoustic microscopy B-scan image data is scaled and interpolated to fuse with the optical coherence tomography B-scan data.
 2. The method of claim 1, wherein the light source is one of a pulsed broadband laser that outputs pulsed broadband light and a swept laser source that outputs pulsed swept laser light of a plurality of wavelengths, wherein the wavelengths are swept in a scan period shorter than 10 nanoseconds.
 3. The method of claim 2, wherein the light source is the swept laser source and the detected photoacoustic waves have energy from the sum of the pulsed swept laser light of the plurality of wavelengths in the scan period.
 4. The method of claim 1, wherein the light source includes a laser and wherein the A-scans for optical coherence tomography and photoacoustic microscopy of the target are generated based on the same photons output by the laser and are co-registered in a lateral direction.
 5. The method of claim 1, wherein generating the fused image further includes establishing a depth relationship between the photoacoustic microscopy B-scan image data and the optical coherence tomography B-scan data.
 6. The method of claim 1, further including moving the light source to a second point on the target to obtain additional A-scans for optical coherence tomography and photoacoustic microscopy of the target.
 7. The method of claim 6, wherein moving the light source to a second point on the target includes scanning the light via an x-y scanner to direct light with respect to the target.
 8. The method of claim 1, further including splitting, via a beam splitter, the light into a sample arm light and a reference arm light.
 9. The method of claim 8, further including: partially reflecting and partially transmitting the reference arm light; detecting, with a photodiode, the reflected reference arm light; and outputting, based on detecting the reflected light with the photodiode, a trigger signal to initiate data acquisition for the photoacoustic microscopy A-scan.
 10. The method of claim 9, further including combining the reflected light, before reaching the detector, with the partially transmitted reference arm light for the optical coherence tomography A-scan.
 11. A optical coherence photoacoustic microscopy controller apparatus comprising: a memory storing instructions for execution; and a computing device configured to at execute the instructions stored in the memory to least: generate, substantially simultaneously using a light source, A-scans for optical coherence tomography and photoacoustic microscopy of a target; form B-scan images for optical coherence tomography and photoacoustic microscopy of the target using the generated A-scans; and generate a fused image of the target from B-scan image data for optical coherence tomography and photoacoustic microscopy, wherein the photoacoustic microscopy B-scan image data is scaled and interpolated to fuse with the optical coherence tomography B-scan data.
 12. The apparatus of claim 11, wherein the light source is one of a pulsed broadband laser that outputs pulsed broadband light and a swept laser source that outputs pulsed swept laser light of a plurality of wavelengths, wherein the wavelengths are swept in a scan period shorter than 10 nanoseconds.
 13. The apparatus of claim 12, wherein the light source is the swept laser source and the detected photoacoustic waves have energy from the sum of the pulsed swept laser light of the plurality of wavelengths in the scan period.
 14. The apparatus of claim 11, wherein the light source includes a laser and wherein the A-scans for optical coherence tomography and photoacoustic microscopy of the target are generated based on the same photons output by the laser and are co-registered in a lateral direction.
 15. The apparatus of claim 11, wherein generating the fused image further includes establishing a depth relationship between the photoacoustic microscopy B-scan image data and the optical coherence tomography B-scan data.
 16. The apparatus of claim 11, wherein the instructions, when execute, further configure the computing device to move the light source to a second point on the target to obtain additional A-scans for optical coherence tomography and photoacoustic microscopy of the target.
 17. The apparatus of claim 16, wherein moving the light source to a second point on the target includes scanning the light via an x-y scanner to direct light with respect to the target.
 18. The apparatus of claim 11, wherein the instructions, when execute, further configure the computing device to split, via a beam splitter, the light into a sample arm light and a reference arm light.
 19. The apparatus of claim 18, wherein the instructions, when execute, further configure the computing device to: partially reflect and partially transmit the reference arm light; detect, with a photodiode, the reflected reference arm light; and output based on detecting the reflected light with, the photodiode, a trigger signal to initiate data acquisition for the photoacoustic microscopy A-scan.
 20. The apparatus of claim 19, wherein the instructions, when execute, further configure the computing device to combine the reflected light, before reaching the detector, with the partially transmitted reference arm light for the optical coherence tomography A-scan. 